Remineralizing Nanomaterials for Minimally Invasive Dentistry

Fig. 9.1

The different zones of dentin caries
Although roots of teeth have a very thin layer of cementum over a large layer of dentin, root caries is mainly caused by demineralization of dentin. Root caries is widespread and increasing in aged adults because pathology and treatment of periodontal diseases expose root surfaces and make them prone to caries attack. It is technically difficult to treat root caries because the lesions tend to “wrap around” the cervical margins of the teeth so that optimal restorative materials are lacking [41]. Therefore, remineralization of dentin is also significant for treatment of root caries. Different in vitro root caries models have been developed for remineralization studies [42].
The etiology of dentin hypersensitivity is ascribed to demineralization that results in exposure of dentinal tubules [15]. Thus, based on a remineralization mechanism, the formation of a mineral layer on the surface of demineralized dentin which results in mineral deposit or plugs in the dentinal tubules is an important therapeutic strategy for dentin hypersensitivity.
The clinical methodologies to deal with carious dental hard tissue can be classified into restorative and nonrestorative repairs [43, 44]. The restorative treatment needs to remove all softened and discoloring dentin to eliminate all infected tissue and create a hard tissue foundation to support a restoration. The use of hand instrumentation and a round steel bur often results in removal of healthy tissue and accidental exposure of the pulp. Moreover, the notion has generally been accepted that restorative intervention is likely the beginning of a long sequence of rerestorations often leading to crowns and implants irrespective of how well the first filling is prepared [44]. The nonrestorative repair for dental caries is in agreement with the concept of MID.
So far, remineralization of superficial enamel caries using fluoride and its derivatives has been well documented in hundreds of completed studies [44]. It has also been demonstrated that fluoride treatment can also facilitate remineralization of shallow dentin and cemetum lesions in vitro [43, 44]. In addition, it was reported that the caries lesion extending to dentin (deep lesion) could be remineralized in vitro although this process is very slow [38]. Now, an emerging view in caries prevention and management is that restorative treatment should be delayed to provide maximum possibilities for natural lesion repair and arrest [38]. Thus, an efficient remineralization strategy for dentin caries is required to achieve a minimally invasive approach for dental caries management.

9.4 Nanomaterials for Remineralization Treatments

The essential feature in the demineralization of dental hard tissues is that a substantial number of mineral ions are removed from the apatite lattice network and its structural integrity is destroyed, leading to the permeability of the dental hard tissues. The possibility of dissolution (demineralization) and formation (remineralization) of HAP depends on the Gibbs free energy change caused by the degree of saturation with respect to HAP, as shown in Eqs. (9.1) and (9.2).


$$ {\mathrm{Ca}}_{10}{\left({\mathrm{PO}}_4\right)}_6{\left(\mathrm{O}\mathrm{H}\right)}_2\underset{\mathrm{Remineralization}}{\overset{\mathrm{Demineralization}}{\rightleftarrows }}10{\mathrm{Ca}}^{2+}+6{\mathrm{PO}}_4+2{\mathrm{OH}}^{-} $$
(9.1)

$$ \varDelta G=RT \ln (S)=RT \ln \left(\mathrm{I}\mathrm{P}/{K}_{\mathrm{sp}}\right) $$
(9.2)

where S is the degree of supersaturation with respect to HAP, R the gas constant (8.314 J · K−1 mol−1), T the absolute temperature, IP the ionic activity product, and K sp the solubility product (K sp for HAP: 2.34 × 10−59) [45]. The IP value for HAP is given by [Ca2+]10[(PO4)3−]6[OH]2γ1 2γ2 10γ3 6, where γz represents the activity coefficient of a z-valent ion. From the point of thermodynamics, if IP < K spG < 0), the solution is unsaturated with respect to HAP, and HAP will dissolve (demineralize); if IP > K spG > 0), the solution is supersaturated, and HAP will form again (remineralize). Since K sp for FAP (fluorapatite, Ca10(PO4)6F2) is 3.16 × 10−60 [45], FAP is more resistant to acid attack than HAP. Therefore, favorable pH value, enough calcium and phosphate ions available, together with adequate fluoride ions are keys for the remineralization of dental hard tissues. Fluoride and calcium phosphate in various forms, such as calcium fluoride, tricalcium phosphate (TCP), hydroxyapatite, fluorohydroxyapatite, and amorphous calcium phosphate (ACP), as the source of fluorine, calcium, and phosphate ions for remineralization of dental hard tissues have been tested for many years. Since a small particle can release ions at higher concentrations, nanoparticles have better ion release profiles than microparticles [46]. Thus, nanoscales of calcium phosphate materials as remineralizing agents have received more attention. Since it is difficult to directly use nanomaterials to remineralize teeth in the oral environment, these materials are often added to restorative materials as inorganic fillers, such as resin composites. It should be noted that these nanomaterials are not used to reinforce the polymer but to release calcium, phosphate, and fluoride ions for remineralization of dental hard tissues.

9.4.1 Calcium Fluoride Nanoparticles

Currently, the effect of fluoride as a preventive agent on dental caries is well established. The role of fluoride in combating caries has been summarized by Wefel [47], ten Cate and Featherstone [48], and Stoodley et al. [49]. Featherstone proposed the three main mechanisms to explain the anticaries effect of fluoride. Firstly, fluoride can inhibit the metabolic and physiological pathways in the cariogenic biofilm that produces organic acids to demineralize dental hard tissues. Secondly, fluoride inhibits demineralization when it replaces ions in hydroxyapatite (HAP) of dental hard tissues to form fluorapatite (FAP) during an acid challenge; FAP is highly resistant to dissolution by acid compared with HAP. Thirdly, fluoride remineralizes dental hard tissue by attaching onto the crystal surface and then attracting calcium ions followed by phosphate ions to nucleate for new mineral formation and growth. Therefore, fluoride treatment is a very important method in minimally invasive dentistry (MID). As remineralizing agents such as sodium fluoride (NaF) and calcium fluoride (CaF2), fluoride has been added to many dental restorative materials (e.g., glass ionomers and resin composites) and preventive products (e.g., dentifrices and mouthwash). The deposits of calcium fluoride (CaF2) and CaF2-like in biofilm, as fluoride (F) reservoir, provide fluoride ions for remineralizaton in oral environment. However, the current fluoride-releasing restorative materials have poor mechanical properties or low fluoride recharge capability [5052].
One approach to resolve this problem is to develop dental composites with fluoride nanoparticles. The CaF2 nanoparticle (nano-CaF2) has a 20-fold higher surface area compared with traditional CaF2 [53, 54]. Thus, the composite with nano-CaF2 shows high fluoride release and still maintains strength and wear resistance [54, 55]. The addition of nano-CaF2 increases cumulative fluoride release; the composites containing 20–30 % nano-CaF2 match the fluoride release rates of traditional glass ionomer materials [53]. Therefore, inhibiting caries by the addition of nano-CaF2 is achieved without compromising long-term mechanical properties of composites [53, 54, 56].

9.4.2 Calcium Phosphate–Based Nanomaterials

Today, nanoparticles of hydroxyapatite (HAP), tricalcium phosphate (TCP), and amorphous calcium phosphate (ACP) have been developed as sources to release calcium/phosphate ions and increase the supersaturation of HAP in carious lesions [5759].

Beta Tricalcium Phosphate (β-TCP, Ca3(PO4)2)

β-TCP serves as a bioactive source of mineralizing components and has been used as a Class II device used in facilitating bone remodeling in maxillofacial procedures (FDA, 2005) and orthopedic applications (FDA, 2003). β-TCP can be functionalized with organic and/or inorganic to form funcionalized β-TCP (fβ-TCP). It has been reported that the combination of fluoride and fTCP produces stronger, more acid-resistant minerals relative to fluoride, native β-TCP, or fTCP alone [60]. As a low-dose system, fTCP does not rely on high levels of calcium and phosphate to drive remineralization [60]. fβ-TCP provides a barrier that prevents premature fluoride–calcium interactions and aids in mineralization when applied via common preparations and procedures [60]. The combination of fluoride plus fTCP has been used to remineralize enamel lesions. Karlinsey et al reported that the combination of NaF (i.e., 500, 950, 1,100, or 5,000 ppm F) plus fTCP in a simple aqueous solution can significantly remineralize white spot enamel lesions relative to that achievable with fluoride alone [60]. In addition, when added to commercial mouth rinse and dentifrice containing fluoride, fTCP provided significantly greater fluoride uptake and rehardening relative to a fluoride-free and controlled fluoride-only mouth rinse and dentifrice [61]. These studies demonstrate that since fTCP can enhance fluoride-based nucleation activity with subsequent remineralization driven by dietary and salivary calcium and phosphate, the combination of fluoride and fTCP appears to be a promising approach to remineralization of dental hard tissues.
Currently, nanoscale β-TCP has been used for bone tissue regeneration due to its higher compressive strength, degradation rate, osteoconductivity, and protein absorption compared to submicron β-TCP [62]. Thus, combination of fluoride and nanomaterials of β-TCP may achieve more effective remineralizing results. However, since β-TCP is often added to mouth rinse and dentifrice, the toxicity of nanoscale β-TCP should be evaluated adequately.

Hydroxyapatite (HAP) Nanoparticles

Synthetic HAP is a biocompatible material, and nano-sized HAP (n-HAP) is similar to the apatite crystal of tooth enamel in morphology and crystal structure. Therefore, it is logical to consider n-HAP as compound substitute for the natural mineral constituent of enamel, with which defects of dental enamel would be repaired.
It has been reported that n-HAP particles can remineralize initial submicrometer enamel caries [63, 64]. If the dimensions of the n-HAP particles are adapted to the scale of the submicrometer- and nano-sized defects, the reparation of the enamel surface can be greatly improved by using these n-HAP particles. It is shown that the basic building blocks of enamel are 20–40 nm HAP nanoparticles [65]. In vitro data indicate that n-HAP with a size of 20 nm fits well with the dimensions of the nanodefects on the enamel surface caused by acidic erosion [64]. Under in vitro conditions, these n-HAP particles can strongly attach to the demineralized enamel surface and inhibit further acidic attack [64]. Thus, the use of well-sized n-HAP particles similar to the scale of the natural building blocks of enamel could de novo repair early carious lesions and thus can protect them from further demineralization to form visible cavities. In the other study, an enamel-like nanocrystal layer with 10 μm thickness in small cavities was achieved in vitro by pasting fluoride-substituted HAP on the enamel within 15 min, but this process was carried out under pH 3.5 and high concentrations of hydrogen peroxide [66]. In view of the real conditions of the oral cavity and potential toxicity of n-HAP, the effect of direct use of n-HAP particles on remineralization of enamel should be further investigated and confirmed in a clinical trial.
n-HAP powder can be also added to dental restorative materials for remineralization effects and improvement of mechanical properties due to its excellent biocompatibility and bioactivity [67, 68]. For instance, compared with micro-HA added to glass ionomer cement, 10 % n-HAP particles (60–100 nm) are incorporated in resin-modified glass ionomer cement, which results in an increased resistance to demineralization and acceptable bonding strength with the only drawback of exceeding the clinically suitable maximum setting time [6971]. Furthermore, the addition of n-HAP and nanofluorohydroxyapatite (n-FHA) to glass ionomer cements increases the compressive, diametral tensile, and biaxial flexural strength of glass ionomer cements [72, 73]. Besides, the glass ionomer cement containing n-FHA has the potential to increase the amount of fluoride release [74].
Nanoparticles of HAP have been incorporated into toothpastes or mouth-rinsing solutions to facilitate the remineralization of demineralized enamel or dentin by depositing HAP nanoparticles in the lesions. Commercially available dental prophylactic products containing biomimetic carbonate hydroxyl apatite nanoparticles have been used to fill microdefects on demineralized enamel or dentin surfaces and proved to be effective in vitro after a 10 min application. However, these promising effects need a clinical study to support them. In addition, the toothpastes with either spheroidal or needle-like particles of n-HAP show better remineralization effect on demineralized enamel than sodium fluoride solutions [75]. However, the in vitro study simulating the real conditions of oral cavity or an in vivo study is needed to further test to prove the remineralization effects of these toothpastes.
Recently, some studies indicated that biomimetic synthesis of hierarchically organized enamel-like structures composed of n-HAP would be an ideal approach to repair enamel microcavities. In the presence of organic additives [7685] or by using various hydrothermal conditions, the in vitro formation of enamel-like microstructures can be achieved. Formation of enamel-like structures in presence of amelogenin, a major extracellular matrix protein in physiological enamel development, has been well documented. Amelogenin oligomers mediate the self-assembly of oriented parallel needle-like apatite bundles to form nano- and microstructured materials, which is compositionally and morphologically similar to natural enamel [25, 76, 7881, 83, 84, 8688]. Amelogenin remineralizes etched enamel surfaces by forming a mineral layer containing needle-like fluoridated HAP crystals with dimensions of 35 nm [80]. Additionally, self-assembling anionic β-sheet peptides, mainly composed of glutamic acid and glutamine, form fibrillar networks as scaffolds to be mineralized and could enhance remineralization and inhibit demineralization of the enamel [82]. Surfactants also can work as micelles or microemulsions to mimic the biomineralization process during the formation of enamel [84]. HAP nanorods modified with monolayers of surfactants can self-assemble into a prism-like enamel structure due to specific surface characteristics [84].
Although some promising in vitro results were obtained, the stability and the mechanical properties of the n-HAP and the enamel-like materials are not sufficient for tooth restorations, and the long time (from several hours to days) for the formation of the mineral structures also limits their clinical application [76, 81]. Therefore, besides remineralization functions, further research should improve the properties of the materials related to clinical operations, thus providing clinically conceivable biomimetic tooth repair.

Amorphous Calcium Phosphate (ACP) Nanoparticles

Amorphous calcium phosphate (ACP) is the initial solid phase precipitating from a highly supersaturated solution with respect to calcium phosphate, which is firstly described by Aaron S. Posner in the mid-1960s [89]. The morphology of ACP particles is shown as small spheroidal particles in the nanoscale (40–100 nm). Owing to its excellent bioactivity, high cell adhesion, adjustable biodegradation rate, and good osteoconduction, ACP has been widely applied in biomedical fields, especially in orthopedic and dental fields [9093]. Since ACP can convert readily to stable crystalline phases such as octacalcium phosphate (OCP) or HAP, it is difficult to directly use ACP to remineralize dental hard tissues unless stabilized in some way. Therefore, like the nanomateirals of CaF2 and HAP mentioned above, ACP nanoparticles, as source of calcium and phosphate ions, have also been added to composite resins, ionomer cements, and adhesives. Taking advantage of the ability of ACP to release calcium and phosphate ions, these composites, especially in the acidic oral environment, present remineralization effects on dental hard tissues to prevent secondary caries after restorations. A study using in situ caries models of humans indicated that nanoACP-containing nanocomposites prevented demineralization at the restoration–enamel margins, producing lower enamel mineral loss compared with the control composite [94]. This result could be attributed to the oral biofilm exposed to nanoACP with higher calcium and phosphorus concentrations than that exposed to the control composite [94]. This high local concentration at the surface thus stimulates precipitation and deposition into tooth structures as apatite mineral. The remineralizing potential of ACP composites can be improved by introducing Si or Zr elements during low-temperature synthesis of the filler [95]. Si and Zr ACPs increased the duration of mineral ion release by slowing down the intracomposite ACP to HAP conversion [96].
Although ACP-containing composites show remineralization ability, these composites exhibit inferior mechanical properties, durability, and water sorption characteristics due to the addition of ACP [97]. These problems could be attributed to the uncontrolled aggregation of ACP nanoparticles along with poor interfacial interaction between them [98]. Currently, stabilizing and coupling agents are used to stabilize and disperse ACP nanoparticles in the composites. It was found that anionic surfactants can stabilize the amorphous solid phase against the conversion to apatite during the precipitation of ACP; the particle size of ACP was also moderately reduced. The hydrophilic polyethylene oxide (PEO) is water compatible due to its multiple hydrogen bonding interactions with water molecules and stabilizes ACP nanoparticles by multiple chelation. Thus, the incorporated PEO in ACP fillers can prevent ACP nanoparticles from aggregating and affect the water content of the ACP-containing composites, which eventually will impact both ion release kinetics and mechanical stability of composites [99].
It has been suggested that ACP works as a precursor to bioapatite and as a transient phase in biomineralization [100]. This process is thought to be mediated by noncollagenous proteins, such as amelogenin, dentin matrix protein (DMP1), and dentin phosphophoryn (DPP, DMP2) with highly phosphorylated serine and threonine. They are biological stabilizers by chelating calcium ions to control the transformation of ACP to HAP. Therefore, it is possible to develop a biomimetic remineralizing strategy for reparation of teeth caries by mimicking the biomineralization process. In the next section, the development of nanocomplexes of stabilizers and ACP will be reviewed.

9.4.3 Nanocomplexes of Stabilizers and Amorphous Calcium Phosphate

Some in vitro studies indicate that some proteins and their derivatives and analogues, such as polymers and poly(amino acid) macromolecules mimicking the functional domain of these proteins, could stabilize calcium/phosphate ions as nanocomplexes of protein/amorphous calcium phosphate (ACP) in solution [101103]. Casein phosphopeptides (CPP) obtained from milk is such an analogue of the proteins involved in biomineralization of teeth.

Nanocomplexes of Casein Phosphopeptides (CPP) and Amorphous Calcium Phosphate (ACP)

The four sequesters of casein phosphopeptides are Bos ɑS1-casein X-5P (f59-79), Bos β-casein X-4P (f1-25), Bos ɑS2-casein X-4P (f46-70), and Bos ɑS2-casein X-4P (f1-21). All the peptides contain the sequence motif -Pse-Pse-Pse-Glu-Glu-, and the major peptides of the preparation are Bos ɑS1-casein X-5P (f59-79) (ab. ɑS1(59–79)) and Bos β-casein X-4P (f1-25) (ab. β (1–25)). It is proposed that the CPP binds to the spontaneously forming ACP nanoclusters under alkaline conditions (e.g. pH 9.0), producing a metastable colloid of nanocomplexes of CPP-ACP. From the stoichiometric and cross-linking analyses [104], the stabilized nanocoplexes of CPP-ACP complex have unit formula of [ɑS1(59–79)(ACP)7]6 and [β(1–25)(ACP)8]6 [105]. A “closed complex” model of β(1–25) complexed with alkaline amorphous calcium phosphate has recently been proposed [104, 105]. This model indicated that all the charged residues of CPP significantly interact with the alkaline calcium phosphate core particle. The hydrodynamic radii of β(1–25)-ACP complex were estimated at 1.526 ± 0.044 nm at pH 6.0 and 1.923 ± 0.082 nm at pH 9.0.
Reynolds et al. developed a routine preparation of nanocomplexes of CPP-ACP by titrating calcium ions, phosphate ions, and hydroxide ions at pH 9.0 into CPP solutions, followed by purifying with filtration and drying. The nanocomplexes of CPP-ACP have been trademarked as RecaldentTM and added to sugar-free gum and dental professional products (GC Tooth MousseTM). Currently, this product is used for the prevention and treatment of early caries and the treatment of tooth sensitivity, especially after in-office bleaching procedures, ultrasonic scaling, hand scaling, and root planing. It was demonstrated that CPP-ACP binds well to Streptococcus mutans in oral biofilm, thereby providing a mineral ion reservoir to release free calcium and phosphate for inhibiting demineralization and enhancing subsequent remineralization [106]. The affinity of CPP-ACP to biofilm could attributed to calcium of CPP-ACP competing the calcium binding sites of biofilm, which will decrease the amount of calcium bridge between bacteria and the acquired pellicle, and among bacteria themselves [107].
In an in vitro caries model, Reynolds et al. investigated the effects of CPP-ACP solutions on remineralization of artificial lesions in human third molars [108]. With 10 day remineralization treatment, 1.0 % CPP-ACP (pH 7.0) solution recovered 63.9 ± 20.1 % of mineral loss [108]. In addition, the combination of CPP-ACP and fluoride has additive remineralizing effects on carious lesions [109]. A recent clinical trial compared the remineralizing effect of a sugar-free gum containing 18.8 mg CPP-ACP with that of a sugar-free gum not containing CPP-ACP on enamel [110]. After in situ remineralisation by the CPP-ACP–containing gum, the lesions with subsequent acid attack showed demineralization beneath the remineralized zone, indicating that the remineralized mineral by CPP-ACP was more resistant to acid challenge [17].
Nanocomplexes of CPP-ACP provide a new effective remineralization method for minimally invasive management of dental caries. Although Reynolds did not emphasize that CPP-ACP is a biomimetic product, but the mechanism of the CPP-stabilized ACP formation is similar to that of phosphorylated protein-stabilized ACP, which transforms into HAP crystal in the process of biomineralization of dental hard tissues. Therefore, inspired from CPP-ACP and understandings on the roles of acidic noncollagenous proteins, such as phosphoproteins, in biomineralization of dental hard tissues, we obtain a strategy for development of novel biomimetic-remineralizing agents for MID: finding analogues of acidic noncollagenous proteins that are capable of stabilizing ACP.

Biomimetic Nanocomplexes of Stabilizer and Amorphous Calcium Phosphate (ACP)

Up to the present, transient amorphous mineral phases have been found in biomineral systems in different phyla of the animalia kingdom [111]. For example, ACP has been reported to form as a precursor phase of carbonated hydroxyapatite in Chiton teeth [112]. Also, an ACP phase has been observed in the newly formed bony zebrafish fin rays [113]. A comprehensive analysis of the mineral phases in the early secretory enamel of the mouse’s mandibular incisor indicated that the outer, younger, early secretory enamel contained a transient disordered ACP phase. The disordered ACP phase is a precursor of crystalline hydroxyapatite and transforms into the final apatitic crystalline mineral with time [111]. It was also suggested that the transient ACP phase can directly deposit inside the gap regions of collagen fibrils during bone and dentin maturation [113].
It is proposed that a variety of acidic noncollagenous proteins are involved in the biomineralization of ACP to HAP [114, 115]. Since the acidic noncollagenous proteins contain aspartic acid and glutamic acid–rich domains, they may act as nucleators or inhibitors, growth modifiers, anchoring molecules, or scaffolds for mineral deposition [116118]. The functional domains of these acidic noncollagenous proteins can be mimicked by some polyelectrolytes and poly(amino acid) macromolecules containing phosphoryl or carboxyl groups, such as polyacrylic acid (PAA) and polyaspartic acid. These biomimetic materials can stabilize ACP and reduce these amorphous phases to nanoscale [119], known as biomimetic nanocomplexes of stabilizer and ACP. This biomimetic process, also known as “polymer-induced liquid precursor” (PILP) [120, 121], has been used to synthesize nanoscale ACP to biomimetically mineralize type I collagen [120, 121]. This biomimetic process has been reported to be independent of ion solubility products and relatively insensitive to changes in pH and osmolarity, which is difficult to be explained by classical crystallization theory. Accordingly, nonclassical crystallization theory (pathway) was proposed to describe the biomimetic mineralization process based on PILP [122]. In the nonclassical pathway, inorganic nanocrystals coated/stablized with organic molecules can form larger mesocrystals via self-assembly and crystallographic alignment. These mesocrystals work as intermediates for the formation of single macroscopic crystals.
Although remineralization of enamel lesions is conceivably achieved and evaluated, the remineralization of dentin is still debatable [15, 38, 123]. Although the deposition of interfibrillar/extrafibrillar apatite minerals can contribute to the increase of the gray intensity value of samples after remineralization, without intrafibrillar mineralization, interfibrillar/extrafibrillar mineralization of dentin alone does not result in a highly mineralized collagen matrix [36] and cannot be regarded as true remineralization of demineralized dentin. Thus, the microradiography as a convincing method for determining the degree of remineralization of enamel [15, 38] has recently been challenged [124].
More recently, based on the rules of nonclassical crystallization pathways, guided tissue remineralization (GTR) was proposed [18]. In their studies, presence of polyacrylic acid (PAA) as calcium phosphate–binding matrix protein analogues or metastable ACP nanoprecursors formed in a Portland cement/phosphate-containing fluid system [18]. Interestingly, only both in the presence of polyvinylphosphonic acid (PVPA) or PAA and sodium trimetaphosphate (STMP) or sodium tripolyphosphate (TPP) as collagen-binding matrix phosphoprotein analogues, the intrafibrillar remineralzation of collagen in dentin was achieved [101, 102]. In guided tissue remineralization, the PAA-based biomimetic analogue is employed as a sequestration agent to stabilize nanoscale ACP that can infiltrate the internal water compartments of a collagen fibril. The phosphorus-based analogue of matrix phosphoproteins binds to the collagen via electrostatic interaction or chemical phosphorylation reactions to attract these nanoprecursors of ACP to the gap zones between the collagen molecules [125]. The self-assembly of nanoprecursors of ACP and their subsequent transformation into nanocrystals of HAP would result in the hierarchical and intrafibrillar remineralization of collagen in demineralized dentin. Therefore, GTR with biomimetic remineralizing materials is potentially useful in the remineralization of partially demineralized caries-affected dentin.
The concepts of CPP-ACP and GTR provide a novel strategy for remineralization treatment in MID. In the concept of CPP-ACP, for remineralization of enamel, one analogue is required to mimic the sequestration function of matrix proteins to stabilize ACP, while in the GTR concept, two polyanionic analogues mimicking the sequestration and templating functions of matrix proteins are involved to stabilize ACP and direct ACP nanoprecursors into collagen molecules for remineralization of dentin. Thus, the analogues stabilizing ACP can aid to remineralize both enamel and dentin.
Only gold members can continue reading. Log In or Register to continue

Oct 11, 2015 | Posted by in Endodontics | Comments Off on Remineralizing Nanomaterials for Minimally Invasive Dentistry
Premium Wordpress Themes by UFO Themes